Composite joint arthroplasty systems and methods

ABSTRACT

A prosthesis may have an articulating component formed via casting and a 3D printed bone anchoring component with a joint-facing side and a bone-facing side. The bone-facing side may have a bone engagement surface with a porous structure with pores selected to facilitate in-growth of the bone into the pores. The bone facing side may further have a surface layer of Titanium Dioxide nanotubes. The joint-facing side may be secured to the articulating component by melting Titanium nanoparticles at a temperature below the melting temperatures of the major constituents of the articulating component and/or the bone anchoring component, such as Cobalt, Chromium, and/or Titanium, so as to avoid significantly modifying the crystalline structures of the articulating component and/or the bone anchoring component. The melting temperature of the Titanium nanoparticles may be about 500° C.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 15/625,802, filed Jun. 16, 2017, entitled “Composite Joint Arthroplasty Systems and Methods”, which claims priority to U.S. Provisional Application Ser. No. 62/466,249 filed on Mar. 2, 2017, entitled “Composite Joint Arthroplasty Systems and Methods”, which are incorporated herein by reference as though set forth in their entirety.

TECHNICAL FIELD

The present disclosure relates to surgical systems and methods. More specifically, the present disclosure relates to implants and related methods for joint arthroplasty.

BACKGROUND

Joint arthroplasty procedures are surgical procedures in which one or more articulating surfaces of a joint are replaced with prosthetic articulating surfaces. Such procedures are becoming increasingly commonplace, for many joints of the body.

For a successful joint arthroplasty, it is important that the implants remain in place and maintain the necessary wear characteristics. Further, it is desirable for the arthroplasty procedure to be carried out quickly and smoothly. Many existing joint arthroplasty implants and methods are time-consuming to implant, do not form a sufficient attachment to the underlying bone, or leave excessive wear debris.

SUMMARY

The various systems and methods of the present disclosure have been developed in response to the present state of the art, and in particular, in response to the problems and needs in the art that have not yet been fully solved by currently available joint arthroplasty systems and methods. The systems and methods of the present disclosure may provide joint implants and instruments that provide enhanced bone fixation, less wear debris, and/or streamlined implantation.

According to some embodiments, a prosthesis may be designed to replace an articular surface on bone. The prosthesis may have an articulating component formed via casting, and a bone anchoring component having a 3D printed structure. The articulating component may have an articulating component joint-facing side with an articular surface, and an articulating component bone-facing side with a bone-facing shape. The bone anchoring component may have a bone anchoring component joint-facing side with a joint-facing shape that is complementary to the bone-facing shape, and a bone anchoring component bone-facing side. The bone anchoring component joint-facing side may be secured to the articulating component bone-facing side. The bone anchoring component bone-facing side may have a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores.

The bone anchoring component may be formed of DMLS (direct metal laser sintered) Titanium, and the 3D printed structure may have a porous structure. The porous structure may have a lower porosity on the bone anchoring component joint-facing side than on the bone anchoring component bone-facing side. The bone anchoring component joint-facing side may have a near solid structure with little or no porosity.

The bone anchoring component bone-facing side may have a surface layer of Titanium Dioxide nanotubes formed via anodization. The Titanium Dioxide nanotubes may have an anatase structure.

The articulating component may be formed of an alloy of Cobalt Chromium. The alloy of Cobalt Chromium may have one or more crystalline structures established by a casting process used to form the articulating component. The bone anchoring component joint-facing side may be secured to the articulating component bone-facing side via a bonding process occurring at a bonding temperature far below melting temperatures of Cobalt and Chromium, such the crystalline structures are not significantly modified by the bonding process. The bonding process may occur at a bonding temperature of about 500° C. The prosthesis may further have a bonding zone, between the bone anchoring component joint-facing side and the articulating component bone-facing side, formed of melted and re-solidified Titanium nanoparticles.

The bone anchoring component joint-facing side may additionally or alternatively be secured to the articulating component bone-facing side via a laser welding process around the perimeter and/or along the seams of the two components. Additionally or alternatively, the two components may also be laser welded along the perimeter and/or seams with the addition of a metallic powder and binder mixture along the weld lines. Specifically, a metal powder and binder mixture may be placed along the weld lines and subsequently melted with a laser. The re-solidified metal may bond the bone anchoring component and the articulating component together. The metallic powder and binder mixture may include titanium powder and a binder consisting of gelatin, glycerin and/or PVA. The metallic powder may additionally or alternatively include a cobalt and chromium powder and a binder consisting of gelatin, glycerin or PVA.

According to some embodiments, a method may be designed for manufacturing a prosthesis for replacing an articular surface on a bone. The method may include casting an articulating component with an articulating component joint-facing side with an articular surface, and an articulating component bone-facing side with a bone-facing shape. The method may further include 3D printing a bone anchoring component with a bone anchoring component joint-facing side with a joint-facing shape that is complementary to the bone-facing shape, and a bone anchoring component bone-facing side with a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores. The method may further include securing the bone anchoring component joint-facing side to the articulating component bone-facing side.

3D printing the bone anchoring component may include direct metal laser sintering Titanium to form a porous structure. Forming the porous structure may include providing lower porosity on the bone anchoring component joint-facing side than on the bone anchoring component bone-facing side.

The method may further include anodizing the bone anchoring component to form a surface layer of Titanium Dioxide nanotubes on the bone anchoring component joint-facing side. The method may further include heating the bone anchoring component to a temperature sufficient to change at least a portion of the surface layer of Titanium Dioxide nanotubes to anatase.

Casting the articulating component may include casting the articulating component from an alloy of Cobalt Chromium. Casting the articulating component may include establishing one or more crystalline structures of the alloy of Cobalt Chromium. Securing the bone anchoring component joint-facing side to the articulating component bone-facing side may include heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to a bonding temperature far below melting temperatures of Cobalt and Chromium, so as to avoid significantly modifying the crystalline structures. The method may further include, prior to heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to the bonding temperature, applying a paste to one or both of the bone anchoring component joint-facing side and the articulating component bone-facing side. The paste may include a gelatin and/or glycerin and Titanium nanoparticles.

The method may further include, after applying the paste on one or both of the bone anchoring component joint-facing side and the articulating component bone-facing side, and prior to heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to the bonding temperature, assembling the articulating component and the bone anchoring component such that the paste is sandwiched between the bone anchoring component joint-facing side and the articulating component bone-facing side, and pressing the bone anchoring component joint-facing side and the articulating component bone-facing side together. Heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to the bonding temperature may include, with the bone anchoring component joint-facing side and the articulating component bone-facing side pressed together, heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side in a two-step heating process to about 500° C. to debind the gelatin/glycerin from the paste and melt the Titanium nanoparticles. The debinding process may be at a temperature below 500° C. and after the gelatin/glycerin is sufficiently removed by debinding, the components may then be heated to about 500° C. for Titanium nanoparticle melting.

In other attachment methods, a laser process may be used to melt the metal of the bone anchoring component and the articulating component along the perimeter and/or along the seams. Additionally or alternatively, a metal powder and binder mixture may be placed along the parameter and seams between the bone anchoring and articulating components and subsequently melted with a laser. The re-solidified metal powder may bond the bone anchoring component and the articulating component together.

Further, according to some embodiments, a method may be designed to manufacture a prosthesis for replacing an articular surface on a bone. The method may include casting metals comprising at least Cobalt and Chromium to form an articulating component with an articulating component joint-facing side with an articular surface, and an articulating component bone-facing side with a bone-facing shape. The method may further include direct metal laser sintering Titanium to form a bone anchoring component with a bone anchoring component joint-facing side with a joint-facing shape that is complementary to the bone-facing shape, and a bone anchoring component bone-facing side with a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores. The method may further include applying a paste containing Titanium nanoparticles to at least one of the bone anchoring component joint-facing side and the articulating component bone-facing side, assembling the articulating component and the bone anchoring component such that the paste is sandwiched between the bone anchoring component joint-facing side and the articulating component bone-facing side, and heating the paste to a bonding temperature sufficient to commence melting of the Titanium nanoparticles to secure the bone anchoring component joint-facing side to the articulating component bone-facing side.

The method may further include anodizing the bone anchoring component to form a surface layer of Titanium Dioxide nanotubes on the bone anchoring component joint-facing side, and, after assembling the articulating component and the bone anchoring component, pressing the articulating component and the bone anchoring component together. The paste may further include gelatin and/or glycerin. Heating the paste to the bonding temperature may include, with the articulating component and the bone anchoring component pressed together, heating at least the bone anchoring component joint-facing side and the articulating component to a temperature below 500° C. to debind the gelatin/glycerin, and then heating the bone anchoring component joint-facing side to about 500° C. to melt the Titanium nanoparticles, and changing at least a portion of the surface layer of Titanium Dioxide nanotubes to anatase.

These and other features and advantages of the present disclosure will become more fully apparent from the following description and appended claims, or may be learned by the practice of the systems and methods set forth hereinafter.

BRIEF DESCRIPTION OF THE DRAWINGS

Exemplary embodiments of the disclosure will become more fully apparent from the following description and appended claims, taken in conjunction with the accompanying drawings. Understanding that these drawings depict only exemplary embodiments and are, therefore, not to be considered limiting of the scope of the appended claims, the exemplary embodiments of the present disclosure will be described with additional specificity and detail through use of the accompanying drawings in which:

FIG. 1 is a perspective view of a knee arthroplasty system according to one embodiment.

FIG. 2 is an exploded, perspective view of the femoral prosthesis of the knee arthroplasty system of FIG. 1.

FIG. 3 is an exploded, perspective view, from a different viewpoint, of the femoral prosthesis of the knee arthroplasty system of FIG. 1.

FIG. 4 is an exploded, perspective view of the tibial prosthesis of the knee arthroplasty system of FIG. 1.

FIG. 5 is an exploded, perspective view, from a different viewpoint, of the tibial prosthesis of the knee arthroplasty system of FIG. 1.

DETAILED DESCRIPTION

Exemplary embodiments of the disclosure will be best understood by reference to the drawings, wherein like parts are designated by like numerals throughout. It will be readily understood that the components of the disclosure, as generally described and illustrated in the Figures herein, could be arranged and designed in a wide variety of different configurations. Thus, the following more detailed description of the embodiments of the apparatus, system, and method, as represented in FIGS. 1 through 5, is not intended to limit the scope of the claims, as claimed, but is merely representative exemplary of exemplary embodiments.

The phrases “connected to,” “coupled to” and “in communication with” refer to any form of interaction between two or more entities, including mechanical, electrical, magnetic, electromagnetic, fluid, and thermal interaction. Two components may be functionally coupled to each other even though they are not in direct contact with each other. The term “abutting” refers to items that are in direct physical contact with each other, although the items may not necessarily be attached together. The phrase “fluid communication” refers to two features that are connected such that a fluid within one feature is able to pass into the other feature.

The word “exemplary” is used herein to mean “serving as an example, instance, or illustration.” Any embodiment described herein as “exemplary” is not necessarily to be construed as preferred or advantageous over other embodiments. While the various aspects of the embodiments are presented in drawings, the drawings are not necessarily drawn to scale unless specifically indicated.

The systems and methods of the present disclosure may be used in connection with a wide variety of implant types. The systems and methods disclosed herein may have particular applicability to implants that benefit from having disparate materials, such as porous materials for bone engagement and hard or nonporous materials for articulation. Thus, the systems and methods set forth herein may be of particular benefit for joint replacement implants. This disclosure focuses on knee arthroplasty implants; however, those of skill in the art will recognize that it may readily be applied to other joint arthroplasty implants, or to implants designed for other purposes besides joint arthroplasty.

FIG. 1 is a perspective view of a knee arthroplasty system, or system 100, according to one embodiment. The system 100 may be designed to replace the natural articulating surfaces of a knee joint, and may thus have a femoral prosthesis 102 and a tibial prosthesis 104. In some embodiments, the system 100 may be designed to replace only the femoral or tibial articulating surfaces, and may thus include only the femoral prosthesis 102 or the tibial prosthesis 104.

The femoral prosthesis 102 and the tibial prosthesis 104 may each have an articulating component with replacement articulating surfaces, and a bone anchoring component secured to the articulating component to secure the articulating component to the underlying bone. Specifically, the femoral prosthesis 102 may have a femoral articulating component 110 and a femoral bone anchoring component 112. Similarly, the tibial prosthesis 104 may have a tibial articulating component 114 and a tibial bone anchoring component 116.

Each of the aforementioned articulating components and bone anchoring components may have a joint-facing side and a bone-facing side. Thus, the femoral articulating component 110 may have a joint-facing side 120 and a bone-facing side 122, and the femoral bone anchoring component 112 may have a joint-facing side 124 and a bone-facing side 126. Similarly, the tibial articulating component 114 may have a joint-facing side 130 and a bone-facing side 132, and the tibial bone anchoring component 116 may have a joint-facing side 134 and a bone-facing side 136.

The bone-facing side 122 of the femoral articulating component 110 may have a shape that matches the shape of the joint-facing side 124 of the femoral bone anchoring component 112, and may be secured to the joint-facing side 124 of the femoral bone anchoring component 112 in a manner that will be set forth in greater detail subsequently. Similarly, the bone-facing side 132 of the tibial articulating component 114 may have a shape that matches the shape of the joint-facing side 134 of the tibial bone anchoring component 116, and may be secured to the joint-facing side 134 of the tibial bone anchoring component 116 in a manner that will be set forth in greater detail subsequently.

The joint-facing side 120 of the femoral articulating component 110 may have a first articulating surface 140 and a second articulating surface 142, which are shaped to mimic the shapes of the natural articulating surfaces on the end of the femur. The shapes depicted in FIG. 1 are merely exemplary; according to alternative embodiments, any articulating surface shape known in the art may be used.

The bone-facing side 126 of the femoral bone anchoring component 112 may have one or more features that enhance engagement of the femoral bone anchoring component 112 with the underlying bone. For example, the bone-facing side 126 of the femoral bone anchoring component 112 may have a pair of posts 150 that protrude from the bone-facing side 126 of the femoral bone anchoring component 112. Optionally, other bone anchoring features (not shown), as known in the art, may be used in addition to or in the alternative to the posts 150.

The joint-facing side 130 of the tibial articulating component 114 may also have a first articulating surface 180 and a second articulating surface 182. After implantation of the femoral prosthesis 102 and the tibial prosthesis 104, the first articulating surface 140 may articulate with the first articulating surface 180, and the second articulating surface 142 may articulate with the second articulating surface 182. The articulation of the femoral articulating component 110 with the tibial articulating component 114 may be designed to mimic that of the natural knee joint.

The bone-facing side 136 of the tibial bone anchoring component 116 may have a plurality of posts 190 that protrude into the bone from the remainder of the bone-facing side 136. Optionally, other bone anchoring features (not shown), as known in the art, may be used in addition to or in the alternative to the posts 190.

FIG. 2 is an exploded, perspective view of the femoral prosthesis 102 of the system 100 of FIG. 1. The femoral articulating component 110 and the femoral bone anchoring component 112 may optionally be manufactured separately from each other. Accordingly, different manufacturing processes may be used to form the femoral articulating component 110 and the femoral bone anchoring component 112. This may advantageously enable the use of materials and/or processes for each of the femoral articulating component 110 and the femoral bone anchoring component 112 that are best suited for the role to be performed.

For example, the femoral articulating component 110 may be designed to endure cyclical loading in friction and compression. Accordingly, high-strength and/or low-wear materials and surface properties may be desired. Accordingly, the femoral articulating component 110 may be made of a relatively hard material such as an alloy of Cobalt Chromium (“Cobalt Chrome,”). Specifically, the femoral articulating component 110 may be made of an alloy of Cobalt Chromium Molybdenum (CoCrMo). A manufacturing process such as casting may be used. In some embodiments, the first articulating surface 140 and the second articulating surface 142 may be specially processed in a manner that increases their hardness and/or wear resistance.

Conversely, the femoral bone anchoring component 112 may be designed to provide high-strength fixation of the femoral articulating component 110 to the underlying bone. It may be desirable for the femoral bone anchoring component 112 to have a porous structure that encourages bone in-growth. Accordingly, the femoral bone anchoring component 112 may be formed of a metal such as Titanium, or specifically, direct metal laser sintered (“DMLS”) Titanium. The femoral bone anchoring component 112 may be formed via an additive manufacturing method such as 3D printing. Such manufacturing methods may facilitate the creation of a porous structure, particularly on the bone-facing side 126 of the femoral bone anchoring component 112.

In some embodiments, the femoral bone anchoring component 112 may be made such that the porosity varies in a gradient through the thickness of the femoral bone anchoring component 112. Thus, the bone-facing side 126 of the femoral bone anchoring component 112 may be made more porous to facilitate bone in-growth, while the joint-facing side 124 of the femoral bone anchoring component 112 may be made less porous to enhance attachment of the joint-facing side 124 to the bone-facing side 122 of the femoral articulating component 110. In some embodiments, the joint-facing side 124 may be made substantially solid (i.e., nonporous) to enhance adhesion to the bone-facing side 122 of the femoral articulating component 110, while the bone-facing side 126 may be highly porous.

As shown, the bone-facing side 122 of the femoral articulating component 110 may have an anterior portion 200, a posterior portion 202, and a distal portion 204. Upon implantation of the femoral articulating component 110, the anterior portion 200 may be located on the anterior side of the knee, the posterior portion 202 may be located on the posterior side of the knee, and the distal portion 204 may be located at the distal end of the femur. The distal portion 204 may be divided into three faces: an anterior-distal face 206, a posterior-distal face 208, and a distal face 210. The anterior-distal face 206 may reside between the anterior portion 200 and the distal face 210, and the posterior-distal face 208 may be reside between the posterior portion 202 and the distal face 210. As shown, the posts 150 may protrude from the distal face 210.

The posts 150 may all protrude in a cephalad direction so that these features can penetrate the bone, helping to anchor the femoral articulating component 110 on the distal end of the femur (not shown). The posts 150 may optionally be shaped to facilitate entry into and/or compaction of the bone. Thus, the bone surrounding the posts 150 in their implanted state may be compacted and/or strengthened.

As also shown in FIG. 2, the bone-facing side 122 of the femoral articulating component 110 may have a peripheral ridge 220 that defines an interior recess 222. The shape of the interior recess 222 may closely match that of the joint-facing side 124 of the femoral bone anchoring component 112 so that the joint-facing side 124 of the femoral bone anchoring component 112 can be secured to the interior recess 222. When the femoral bone anchoring component 112 and the femoral articulating component 110 are assembled together, the bone-facing side 126 of the femoral bone anchoring component 112 may lie substantially flush with the peripheral ridge 220 of the bone-facing side 122 of the femoral articulating component 110.

In some embodiments, the bone-facing side 126 of the femoral bone anchoring component 112 may be treated to enhance porosity and/or bone in-growth. In some examples, the bone-facing side 126 of the femoral bone anchoring component 112 may be processed via a process such as anodizing to form Titanium Dioxide nanotubes on the bone-facing side 126. Specifically, the bone-facing side 126 may be anodized in a Fluoride electrolyte, as set forth in U.S. application Ser. No. 11/913,062, filed Jun. 10, 2008 and entitled “Compositions Comprising Nanostructures for Cell, Tissue and Artificial Organ Growth, and Methods for Making and Using Same, now U.S. Pat. No. 8,414,908, which is incorporated by reference as though set forth herein in its entirety. The result may be the formation of a surface layer 230 of Titanium Dioxide nanotubes on the bone-facing side 126.

The femoral articulating component 110 and the femoral bone anchoring component 112 may be secured together in a variety of ways. One exemplary attachment method will be set forth as follows. Those of skill in the art will recognize that various steps set forth below may be omitted, replaced with alternative steps, and/or supplemented with additional steps not specifically provided herein. Further, the following steps are not limited to knee implants, but may be used in connection with any implant having an articulating component and a bone engagement component.

A paste 240 may be made from nanoparticles of a metal such as commercially pure Titanium. The nanoparticles may be formed in a variety of ways. According to one embodiment, Titanium nanoparticles may be made by ball milling a Titanium halide such as Titanium Chloride, with a metal reactant such as Magnesium. However, other metals, such as those of group 1 and group 2, may be used for the reactant. The mechanical action and formation of salt byproduct may prevent particle growth and produce fine particles. The salt byproduct may be removed via solvation in water or an aprotic solvent with a high dielectric constant, such as formaldehyde. Further details may be found in Blair, R. G., E. G. Gillan, N. K. B. Nguyen, D. Daurio, and R. B. Kaner, Rapid solid-state synthesis of titanium aluminides. Chemistry of Materials, 2003. 15(17): p. 3286-3293, and in Restrepo, D., S. M. Hick, C. Griebel, J. Alarcon, K. Giesler, Y. Chen, N. Orlovskaya, and R. G. Blair, Size controlled mechanochemical synthesis of ZrSi ₂. Chemical Communications, 2013. 49: p. 707-709.

The result may be formation of nanoparticles of Titanium. The nanoparticles may be less than 20 nm in cross-sectional size, and need not be spherical but may instead be flake-shaped. The nanoparticles may thus have a melting temperature much lower than that of bulk Titanium. In order to provide a consistently lowered melting temperature, it may be desirable to provide the nanoparticles in a fairly tight Gaussian distribution, for example, 15 nm average size, +/−5 nm. Even a few particles greater than 25 nm in size may cause the melting temperature to rise. The low melting temperature may help the nanoparticles to melt into the adjoining material (for example, CrCo and Ti) and mechanically bond therewith, rather than diffusion bonding, as will be discussed subsequently.

The Titanium nanoparticles may be added to material such as a gelatin and/or glycerin to form the paste 240. The paste may be applied to one or both of the surfaces to be secured together, which, for the femoral prosthesis 102, may be the joint-facing side 124 of the femoral bone anchoring component 112 and the interior recess 222 of the bone-facing side 122 of the femoral articulating component 110. The paste 240 depicted in FIG. 2, on the joint-facing side 124 and the interior recess 222 is merely exemplary; it may be advantageous to spread the paste 240 over substantially the entire surface of the joint-facing side 124 or the interior recess 222.

The paste 240 may be applied in a variety of ways, such as spraying the surface to be coated, immersing the surface to be coated in a quantity of the paste, and/or spreading the paste 240 on the surface with a brush or other implement. The use of the gelatin and/or glycerin may facilitate adhesion of the paste 240 to the joint-facing side 124 and the bone-facing side 122.

The femoral articulating component 110 and the femoral bone anchoring component 112 may then be assembled together such that the joint-facing side 124 of the femoral bone anchoring component 112 is in contact with the bone-facing side 122 of the femoral articulating component 110. The femoral articulating component 110 and the femoral bone anchoring component 112 may be compressed together. In some embodiments, this may be done by positioning the femoral articulating component 110 above the femoral bone anchoring component 112, so that the weight of the femoral articulating component 110 urges the femoral articulating component 110 against the femoral bone anchoring component 112. Alternatively, a carbon fixture or other implement may be used to urge the femoral articulating component 110 and the femoral bone anchoring component 112 together.

The femoral articulating component 110 and the femoral bone anchoring component 112 may then be placed into a vacuum furnace or other heating implement. If desired, the femoral articulating component 110 and the femoral bone anchoring component 112 may continue to be compressed together as these parts are inserted into the furnace and heated. The furnace may then be used to heat the femoral articulating component 110 and the femoral bone anchoring component 112.

As the temperature of the femoral articulating component 110 and/or the femoral bone anchoring component 112 reaches about 200-300° C., the gelatin and/or glycerin may be burned away (debind process), and Carbon may be outgassed from the partial pressure vacuum furnace via an inert carrier gas. The Titanium nanoparticles may be left with air between their spheres. The furnace may be used to further heat the femoral articulating component 110 and the femoral bone anchoring component 112 to a bonding temperature of about 500° C., at which the Titanium nanoparticles may begin to melt, securing the joint-facing side 124 of the femoral bone anchoring component 112 to the bone-facing side 122 of the femoral articulating component 110. The femoral articulating component 110 and the femoral bone anchoring component 112 may then be removed from the furnace and allowed to cool.

At the bonding temperature, the Titanium Dioxide nanotubes may turn into anatase. This may be advantageous because, when compared with amorphous Titanium Dioxide, anatase may have greater strength and superior bone bonding characteristics. Thus, the surface properties of the bone-facing side 126 of the femoral bone anchoring component 112 may be enhanced by the process used to bond the femoral bone anchoring component 112 to the femoral articulating component 110.

Advantageously, the maximum temperature of this process may be the bonding temperature, which may be much lower than the melting temperatures of the significant constituent metals of which the femoral articulating component 110 is formed. Specifically, the melting temperature of Cobalt is 1,995° C., the melting temperature of Chromium is 1,907° C., and the melting temperature of Molybdenum is 2,623° C. Thus, the bonding process used to secure the femoral articulating component 110 to the femoral bone anchoring component 112 may not change the crystalline structure of the femoral bone anchoring component 112, as determined by the manufacturing process (for example, casting) used to form the femoral bone anchoring component 112. Thus, formation of brittle alloys may be avoided, which may occur in known processes in which conventional Titanium is diffusion bonded to Cobalt Chromium Molybdenum.

In addition to or in the alternative to the use of Titanium nanoparticles, a variety of other metals may be used to bond the femoral articulating component 110 to the femoral bone anchoring component 112. Nanoparticles of metals often have melting temperatures lower than those of the corresponding bulk metals; accordingly, a wide variety of nanoparticles, including Titanium, Cobalt, and Chromium nanoparticles, may be used. Additionally or alternatively, metals with lower melting temperatures than Titanium, Cobalt, and Chromium may be used in bulk, rather than nanoparticle, form. For example, Nitinol has a melting temperature of about 1400° C., which is also lower than the melting temperatures of Titanium, Cobalt, and Chromium. Thus, the paste 240, in some embodiments may include a Nitinol powder, which need not be in the form of nanoparticles.

The bond formed between the joint-facing side 124 of the femoral bone anchoring component 112 and the bone-facing side 122 of the femoral articulating component 110 may be a physical bond rather than a metallurgical bond. Thus, the Titanium nanoparticles may flow into surface irregularities in the joint-facing side 124 of the femoral bone anchoring component 112 and/or the bone-facing side 122 of the femoral articulating component 110 so that, when the Titanium nanoparticles re-freeze, they secure the femoral articulating component 110 and the femoral bone anchoring component 112 together. Avoidance of a metallurgical bond is advantageous in that such bonds can disrupt the crystalline structure of the materials being bonded. Thus, the low bonding temperature of the method set forth herein has many advantages, and may provide the femoral prosthesis 102 with enhanced wear resistance and/or bone adhesion.

A second attachment method may be used in addition to or in the alternative to the foregoing. The femoral bone anchoring component 112 may be placed in the interior recess 222 of the bone-facing side 122 of the femoral articulating component 110. A laser may be used to melt the metal of both components together along the perimeter and/or along the seams between the femoral bone anchoring component 112 and the femoral articulating component 110.

A third attachment method may be used in addition to or in the alternative to either or both of the foregoing. A metallic powder and binder mixture may be placed along the perimeter and/or the seams of the femoral bone anchoring component 112 prior to placement of the femoral bone anchoring component 112 in the interior recess 222 of the bone-facing side 122 of the femoral articulating component 110. A laser may be used to melt the metal powder and binder mixture along the perimeter and/or the seams. The re-solidified metal may bond the femoral bone anchoring component 112 and the femoral articulating component 110 together.

In addition to or in the alternative to the foregoing attachment methods, the methods disclosed in U.S. application Ser. No. 10/455,846, filed Jun. 6, 2003 and entitled “METHOD FOR ATTACHING A POROUS METAL LAYER TO A METAL SUBSTRATE,” now U.S. Pat. No. 6,945,448, may be used. This application is incorporated as though set forth herein in its entirety.

The same method (or a similar method) may be used to secure the tibial articulating component 114 to the tibial bone anchoring component 116. Further, as mentioned previously, such bonding methods may be used not just for knee implants, but for other types of implants, and in particular, orthopedic implants in which an articulating component is to be secured to a bone anchoring component.

The method set forth above may be effective for relatively smooth surfaces. However, if desired, the surfaces to be bonded together may have features that facilitate and/or enhance the results of the bonding process. For example, the bone-facing side 122 of the femoral articulating component 110 may have features that cooperate with corresponding features (shown in FIG. 4) on the joint-facing side 124 of the femoral bone anchoring component 112 to help align the femoral articulating component 110 with the femoral bone anchoring component 112 and/or add mechanical fastening to the bonding described above. These features of the bone-facing side 122 may include, by way of example, a pair of post bosses 250.

FIG. 3 is an exploded, perspective view, from a different viewpoint, of the femoral prosthesis 102 of the system 100 of FIG. 1. The joint-facing side 124 of the femoral bone anchoring component 112 and the joint-facing side 120 of the femoral articulating component 110 are more clearly visible.

As shown, the joint-facing side 124 of the femoral bone anchoring component 112 may have features that cooperate with the post bosses 250 of the bone-facing side 122 of the femoral articulating component 110 depicted in FIG. 2. These features may include, for example, post bores 350. Each of the post bores 350 may reside in the interior of one of the posts 150. The post bores 350 may be shaped to receive the post bosses 250. If desired, the post bosses 250 may each be tapered to facilitate insertion into the post bores 350.

The features of the bone-facing side 122 may be received by these features of the joint-facing side 124 with some interference, which may cooperate with the bond described above to enhance attachment of the bone-facing side 122 to the joint-facing side 124. When the femoral articulating component 110 and the femoral bone anchoring component 112 are compressed together, as set forth above, the compression may be sufficient to urge the post bosses 250 into the post bores 350.

Additionally or alternatively, the heat applied to the femoral articulating component 110 and the femoral bone anchoring component 112 may cause thermal expansion eases insertion of the post bosses 250 into the post bores 350. The femoral articulating component 110 may be made such that the femoral articulating component 110 has higher thermal expansion than the femoral bone anchoring component 112. Thus, after insertion of the bosses into the bores, the femoral articulating component 110 and the femoral bone anchoring component 112 may be cooled, allowing the bores to tighten around the bosses.

In alternative embodiments, other positive and/or negative features may be used. Further, if desired, the positive features may be on the joint-facing side 124 of the femoral bone anchoring component 112, and the negative features may be on the bone-facing side 122 of the femoral articulating component 110.

FIG. 4 is an exploded, perspective view of the tibial prosthesis 104 of the system 100 of FIG. 1. As with the femoral prosthesis 102, the tibial articulating component 114 and the tibial bone anchoring component 116 may optionally be manufactured separately from each other. Accordingly, different manufacturing processes may be used to form the tibial articulating component 114 and the tibial bone anchoring component 116. For example, the tibial articulating component 114 may be formed via casting, and the tibial bone anchoring component 116 may be formed via additive manufacturing such as 3D printing.

Like the femoral articulating component 110, the tibial articulating component 114 may be made of Cobalt Chromium, or Cobalt Chromium Molybdenum. Similarly, like the femoral bone anchoring component 112, the tibial bone anchoring component 116 may be made of DMLS Titanium. A gradient of porosities may be present in the tibial bone anchoring component 116, with greater porosity on the bone-facing side 136, and lesser porosity on the joint-facing side 134. If desired, the joint-facing side 134 may be made substantially nonporous to enhance adhesion to the tibial articulating component 114, and the bone-facing side 136 may have a high level of porosity to promote bone in-growth.

As shown, the bone-facing side 132 of the tibial articulating component 114 may have a central plateau 400 that extends toward the tibial bone anchoring component 116, and a peripheral recess 402 that encircles the central plateau 400 and is recessed from the tibial bone anchoring component 116. The joint-facing side 134 of the tibial bone anchoring component 116 may have a shape that is complementary to that of the bone-facing side 132 of the tibial articulating component 114. Specifically, the joint-facing side 134 may have a peripheral ridge 410 that encircles an interior recess 412. An alcove 414 may extend into the peripheral ridge 410, from the space above the interior recess 412. When the tibial articulating component 114 and the tibial bone anchoring component 116 are assembled together, the central plateau 400 may be received within the interior recess 412, and the peripheral ridge 410 may engage the central plateau 400.

In some embodiments, the tibial articulating component 114 and the tibial bone anchoring component 116 may be secured together by the same bonding process described above in connection with the femoral articulating component 110 and the femoral bone anchoring component 112 of the femoral prosthesis 102, or with a modified version of such a bonding process. Thus, FIG. 4 depicts the exemplary application of the paste 240 to the interior recess 412 of the joint-facing side 134 of the tibial bone anchoring component 116.

FIG. 5 is an exploded, perspective view, from a different viewpoint, of the tibial prosthesis 104 of the system 100 of FIG. 1. As shown, the central plateau 400 of the bone-facing side 132 of the tibial articulating component 114 may have a lip 500 that protrudes anteriorly. When the tibial articulating component 114 and the tibial bone anchoring component 116 are assembled, the lip 500 may protrude into the alcove 414 depicted in FIG. 4. Engagement of the lip 500 and the alcove 414 may further help to hold the anterior portions of the tibial articulating component 114 and the tibial bone anchoring component 116 together.

FIG. 5 also depicts the bone-facing side 136 of the tibial bone anchoring component 116 in greater detail. Four of the posts 190 may be present on the bone-facing side 136, and may help enhance the level of engagement of the bone-facing side 136 with the underlying bone, and in particular, with the cortical bone at the proximal end of the tibia. The posts 190 may also increase the surface area of the bone-facing side 136 in contact with the bone of the tibia, thereby further enhancing the potential for bone cement bonding and/or bone in-growth between the tibia and the bone-facing side 136.

Further, if desired, the tibial bone anchoring component 116 may be processed as described above in the description of the femoral bone anchoring component 112, such that the tibial bone anchoring component 116 has a surface layer 230 formed of Titanium Dioxide nanotubes. Such a surface layer 230 may further enhance bone in-growth to further secure the bone-facing side 136 to the bone of the tibia.

As mentioned previously, the tibial articulating component 114 and the tibial bone anchoring component 116 may be secured together through the use of a method like that set forth in the description of the femoral articulating component 110 and the femoral bone anchoring component 112. In the course of such a method, the paste 240 may be applied to the bone-facing side 132 of the tibial articulating component 114 and/or to the joint-facing side 134 of the tibial bone anchoring component 116.

Any methods disclosed herein comprise one or more steps or actions for performing the described method. The method steps and/or actions may be interchanged with one another. In other words, unless a specific order of steps or actions is required for proper operation of the embodiment, the order and/or use of specific steps and/or actions may be modified.

Reference throughout this specification to “an embodiment” or “the embodiment” means that a particular feature, structure or characteristic described in connection with that embodiment is included in at least one embodiment. Thus, the quoted phrases, or variations thereof, as recited throughout this specification are not necessarily all referring to the same embodiment.

Similarly, it should be appreciated that in the above description of embodiments, various features are sometimes grouped together in a single embodiment, Figure, or description thereof for the purpose of streamlining the disclosure. This method of disclosure, however, is not to be interpreted as reflecting an intention that any claim require more features than those expressly recited in that claim. Rather, as the following claims reflect, inventive aspects lie in a combination of fewer than all features of any single foregoing disclosed embodiment. Thus, the claims following this Detailed Description are hereby expressly incorporated into this Detailed Description, with each claim standing on its own as a separate embodiment. This disclosure includes all permutations of the independent claims with their dependent claims.

Recitation in the claims of the term “first” with respect to a feature or element does not necessarily imply the existence of a second or additional such feature or element. Elements recited in means-plus-function format are intended to be construed in accordance with 35 U.S.C. § 112 Para. 6. It will be apparent to those having skill in the art that changes may be made to the details of the above-described embodiments without departing from the underlying principles set forth herein.

While specific embodiments and applications of the present disclosure have been illustrated and described, it is to be understood that the scope of the appended claims is not limited to the precise configuration and components disclosed herein. Various modifications, changes, and variations which will be apparent to those skilled in the art may be made in the arrangement, operation, and details of the methods and systems disclosed herein. 

What is claimed is:
 1. A prosthesis for replacing an articular surface on bone, the prosthesis comprising: an articulating component formed via casting, the articulating component comprising: an articulating component joint-facing side comprising an articular surface; and an articulating component bone-facing side comprising a bone-facing shape; and a bone anchoring component having a 3D printed structure, the bone anchoring component comprising: a bone anchoring component joint-facing side comprising a joint-facing shape that is complementary to the bone-facing shape, wherein the bone anchoring component joint-facing side is secured to the articulating component bone-facing side; and a bone anchoring component bone-facing side comprising a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores.
 2. The prosthesis of claim 1, wherein: the bone anchoring component is formed of DMLS Titanium; and the 3D printed structure comprises a porous structure.
 3. The prosthesis of claim 2, wherein the porous structure has a lower porosity on the bone anchoring component joint-facing side than on the bone anchoring component bone-facing side.
 4. The prosthesis of claim 1, wherein the bone anchoring component joint-facing side comprises a surface layer of Titanium Dioxide nanotubes formed via anodization.
 5. The prosthesis of claim 4, wherein the Titanium Dioxide nanotubes comprise an anatase structure.
 6. The prosthesis of claim 1, wherein: the articulating component is formed of an alloy of Cobalt Chromium comprising one or more crystalline structures established by a casting process used to form the articulating component; and the bone anchoring component joint-facing side is secured to the articulating component bone-facing side via a bonding process occurring at a bonding temperature far below melting temperatures of Cobalt and Chromium, such the crystalline structures are not significantly modified by the bonding process.
 7. The prosthesis of claim 6, wherein: the bonding process occurs at a bonding temperature, at the bone anchoring component joint-facing side and the articulating component bone-facing side, of about 500° C.; and the prosthesis further comprises a bonding zone, between the bone anchoring component joint-facing side and the articulating component bone-facing side, formed of melted and re-solidified Titanium nanoparticles.
 8. The prosthesis of claim 6, wherein: the bonding process occurs via laser welding a perimeter and/or seams of the bone anchoring component joint-facing side and the articulating component bone-facing side together; and the prosthesis further comprises a bonding zone at the perimeter and/or seams, formed of melted and re-solidified Titanium, Cobalt, and/or Chromium nanoparticles.
 9. A method for manufacturing a prosthesis for replacing an articular surface on a bone, the method comprising: casting an articulating component comprising: an articulating component joint-facing side comprising an articular surface; and an articulating component bone-facing side comprising a bone-facing shape; and 3D printing a bone anchoring component comprising: a bone anchoring component joint-facing side comprising a joint-facing shape that is complementary to the bone-facing shape; and a bone anchoring component bone-facing side comprising a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores; and securing the bone anchoring component joint-facing side to the articulating component bone-facing side.
 10. The method of claim 9, wherein 3D printing the bone anchoring component comprises direct metal laser sintering Titanium to form a porous structure.
 11. The method of claim 9, wherein forming the porous structure comprises providing lower porosity on the bone anchoring component joint-facing side than on the bone anchoring component bone-facing side.
 12. The method of claim 9, further comprising anodizing the bone anchoring component to form a surface layer of Titanium Dioxide nanotubes on the bone anchoring component joint-facing side.
 13. The method of claim 12, further comprising heating the bone anchoring component to a temperature sufficient to change at least a portion of the surface layer of Titanium Dioxide nanotubes to anatase.
 14. The method of claim 9, wherein: casting articulating component comprises casting the articulating component from an alloy of Cobalt Chromium to establish one or more crystalline structures of the alloy of Cobalt Chromium; and securing the bone anchoring component joint-facing side to the articulating component bone-facing side comprises heating at least part of the bone anchoring component and at least part of the articulating component to a bonding temperature far below melting temperatures of Cobalt and Chromium, so as to avoid significantly modifying the crystalline structures.
 15. The method of claim 14, wherein heating at least part of the bone anchoring component and part of the articulating component to the bonding temperature comprises laser welding a perimeter and/or seams of the bone anchoring component joint-facing side and the articulating component bone-facing side together.
 16. The method of claim 14, further comprising, prior to heating at least part of the bone anchoring component and part of the articulating component to the bonding temperature, applying a paste to one or both of the bone anchoring component joint-facing side and the articulating component bone-facing side, the paste comprising Titanium nanoparticles and a gelatin and/or a glycerin.
 17. The method of claim 16, further comprising, after applying the paste on one or both of the bone anchoring component joint-facing side and the articulating component bone-facing side, and prior to heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to the bonding temperature: assembling the articulating component and the bone anchoring component such that the paste is sandwiched between the bone anchoring component joint-facing side and the articulating component bone-facing side; and pressing the bone anchoring component joint-facing side and the articulating component bone-facing side together.
 18. The method of claim 17, wherein heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to the bonding temperature comprises, with the bone anchoring component joint-facing side and the articulating component bone-facing side pressed together, heating at least the bone anchoring component joint-facing side and the articulating component bone-facing side to about 500° C. to debind the gelatin and/or glycerin and melt the Titanium nanoparticles.
 19. A method for manufacturing a prosthesis for replacing an articular surface on a bone, the method comprising: casting metals comprising at least Cobalt and Chromium to form an articulating component comprising: an articulating component joint-facing side comprising an articular surface; and an articulating component bone-facing side comprising a bone-facing shape; and direct metal laser sintering Titanium to form a bone anchoring component comprising: a bone anchoring component joint-facing side comprising a joint-facing shape that is complementary to the bone-facing shape; and a bone anchoring component bone-facing side comprising a bone engagement surface having a porous structure with pores selected to facilitate in-growth of the bone into the pores; applying a paste containing Titanium nanoparticles to at least one of the bone anchoring component joint-facing side and the articulating component bone-facing side; assembling the articulating component and the bone anchoring component such that the paste is sandwiched between the bone anchoring component joint-facing side and the articulating component bone-facing side; and heating the paste to a bonding temperature sufficient to commence melting of the Titanium nanoparticles to secure the bone anchoring component joint-facing side to the articulating component bone-facing side.
 20. The method of claim 19, further comprising: anodizing the bone anchoring component to form a surface layer of Titanium Dioxide nanotubes on the bone anchoring component joint-facing side; and after assembling the articulating component and the bone anchoring component, pressing the articulating component and the bone anchoring component together; wherein: the paste further comprises a gelatin and/or a glycerin; and heating the paste to the bonding temperature comprises, with the articulating component and the bone anchoring component pressed together, heating at least the bone anchoring component joint-facing side and the articulating component to about 500° C. to debind the gelatin and/or glycerin, melt the Titanium nanoparticles, and changing at least a portion of the surface layer of Titanium Dioxide nanotubes to anatase. 